|Publication number||US7463926 B1|
|Application number||US 11/166,618|
|Publication date||Dec 9, 2008|
|Filing date||Jun 24, 2005|
|Priority date||Jun 24, 2005|
|Also published as||US8082036, US20090082826|
|Publication number||11166618, 166618, US 7463926 B1, US 7463926B1, US-B1-7463926, US7463926 B1, US7463926B1|
|Inventors||Paul A. Levine, Arndt Godau|
|Original Assignee||Pacesetter, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (25), Referenced by (1), Classifications (9), Legal Events (3)|
|External Links: USPTO, USPTO Assignment, Espacenet|
The invention relates to the field of implantable medical devices and more particularly to devices and algorithms for automatically evaluating and adjusting sensing for improved detection, particularly of irregular waveforms.
Many implantable medical devices include among their operation the sensing and detection of one or more physiological parameters. Such devices may include one or more implantable sensing electrodes and typically include corresponding signal amplifier and sensing circuits. As used herein, “sensing” refers to developing a signal (such as an electrical potential) corresponding to one or more physiological parameters and the sensing can occur continuously and/or on a periodic or sampled basis. “Detection” refers to the determination of the sensed signal as corresponding to the occurrence or lack thereof of a given physiological process.
Some difficulties faced with accurately sensing and detecting physiological processes, such as with an implantable medical device, include that many physiological parameters of interest generate relatively low level base signals and are frequently presented in a background of relatively wide band noise which may be of greater magnitude than the signals of the physiological process of interest. A further difficulty is that a physiological process of interest may be of irregular or intermittent nature thus complicating accurate detection, e.g. whether a given physiological process is absent, delayed, premature, or of smaller magnitude than expected. For one example, implantable cardiac stimulation devices such as pacemakers and/or cardioverter defibrillators (ICDs) automatically sense the patient's cardiac activity by deriving electrical signals from the electrochemical activity of the heart, use these sensed signals to detect the presence/absence, magnitude of, and relative timing of activity in cardiac tissue and automatically supply therapeutic electrical stimulation as indicated to provide desired cardiac rhythm.
In implantable medical devices, such as pacemakers and ICDs, electrical signals picked up by one or more sensing electrode in contact with the patient's cardiac tissue is conducted by one or more leads to battery powered sensing circuitry typically contained within a hermetically sealed biocompatible housing or can which is also implanted within the patient. The sensing circuitry typically includes variable gain amplifier and detection circuitry which evaluates the amplified signals sensed from the patient's cardiac tissue for determination of presence and timing of cardiac activity of interest. A threshold is typically set such that sensing of a cardiac signal within a given time window and above the threshold constitutes “detection” of the corresponding physiological process, such as an atrial or ventricular contraction. The gain of the amplifier and the setting of the threshold is preferably set such that the device accurately senses and detects cardiac activity occurring with reduced incidence of failure to detect such activity (undersensing) as well as reduced incidence of falsely “detecting” signals as corresponding to a physiological process not actually present (oversensing). However, such setting of the gain and thresholds is complicated by the variable timing and magnitudes of the signals of interest particularly in patients for whom implantation of a cardiac stimulation device is indicated.
A variety of devices and algorithms are known which attempt to more accurately determine and set appropriate gain and threshold settings for an implantable medical device and patient combination. Such devices and algorithms may operate automatically within the device itself and/or may operate in a command manner via an external device in communication with the implantable device, such as a physician's programmer. Setting and evaluation of amplifier gains and thresholds may occur at initial implantation as well as periodically throughout the implant lifetime.
For example, one process for setting the sensing thresholds involves establishing communication between an implantable cardiac stimulation device and an external physician's programmer. A clinician then commands, via the physician's programmer, the implantable device to progressively program itself to less sensitive settings. The performance of the implantable device with the progressively less sensitive settings is evaluated with respect to independent measurement of the patient's cardiac activity via a surface electrocardiogram (ECG) and loss of sensing is recognized by either competition between intrinsic and paced activity or failure of the device to indicate an appropriate sense marker despite visible observation of the native signal by the surface ECG. The clinician would terminate the test and use this data to then program the most appropriate threshold settings. A refinement of this general process is also known wherein, upon initiation of the test, the test proceeds automatically with communication between the programmer and the implantable device. However, these processes are subject to misinterpretation leading to instances of suspect results which will be discussed in greater detail below.
One theoretically possible remedy for more accurately conducting sensing measurement tests, such as sensing of the P and R waves of a patient's cardiac cycle, is to perform relatively high frequency sampling of the wave forms to much more accurately obtain information relating to the magnitude and timing of these physiological signals. However, in practical application, this has not proven a viable possibility. Firstly, the microprocessor and memory resources of the implantable device are limited in capacity and the allocation of the necessary processing resources to support very high rate sampling has not proven feasible. Secondly, relatively high rate sampling is also relatively demanding of the limited energy capacity of the battery and thus employing high rate sampling, particularly on a periodic basis to re-verify or adjust sensing threshold throughout the implantation period unacceptably drains the battery indicating an early invasive procedure to replace the battery.
Thus, from the forgoing it will be appreciated that there is a need for a system that can more accurately determine appropriate sensing threshold parameters in an implantable medical device, such as in an implantable cardiac stimulation device, to facilitate more accurate detection of physiological processes of interest. There is a particular need for a system of setting such sensing threshold parameters in applications where the subjects' physiological processes generate indicia that are irregular in nature over time. It would be further advantageous for such a system to be provided in a manner that is substantially automated to reduce operating burden on clinicians or other users of the system.
Preferred embodiments provide a system and method for automatically testing the measurement of one or more physiological processes by an implantable medical device. The sensing of the physiological process is evaluated and a pattern of the process is determined, such as a regular periodicity or a repetition of an irregular complex. The determined pattern can be used for predictive purposes. For example, in one embodiment, a more aggressive set of sensing parameters is iteratively temporarily set and the pattern is redetermined until a change in the pattern indicates that the more aggressive set of sensing parameters has led to at least a partial loss of detection. The system can store the information and report this result for evaluation by a clinician and/or can use the result for possible refinement of the programmed sensing parameters.
Reference will now be made to the drawings wherein like numerals refer to like parts throughout. The following description is of the best mode presently contemplated for practicing the invention. This description is not to be taken in a limiting sense but is made merely for the purpose of describing the general principles of the invention. The scope of the invention should be ascertained with reference to the issued claims. In the description of the invention that follows, like numerals or reference designators will be used to refer to like parts or elements throughout.
In one embodiment, as shown in
To sense left atrial and ventricular cardiac signals and to provide left chamber pacing therapy, the stimulation device 10 is coupled to a “coronary sinus” lead 24 designed for placement in the “coronary sinus region” via the coronary sinus ostium (OS) for positioning a distal electrode adjacent to the left ventricle and/or additional electrode(s) adjacent to the left atrium. As used herein, the phrase “coronary sinus region” refers to the vasculature of the left ventricle, including any portion of the coronary sinus, great cardiac vein, left marginal vein, left posterior ventricular vein, middle cardiac vein, and/or small cardiac vein or any other cardiac vein accessible by the coronary sinus.
Accordingly, an exemplary coronary sinus lead 24 is designed to receive atrial and ventricular cardiac signals and to deliver left ventricular pacing therapy using at least a left ventricular tip electrode 26, left atrial pacing therapy using at least a left atrial ring electrode 27, and shocking therapy using at least a left atrial coil electrode 28.
The stimulation device 10 is also shown in electrical connection with the patient's heart 12 by way of an implantable right ventricular lead 30 having, in this embodiment, a right ventricular tip electrode 32, a right ventricular ring electrode 34, a right ventricular (RV) coil electrode 36, and a superior vena cava (SVC) coil electrode 38. Typically, the right ventricular lead 30 is transvenously inserted into the heart 12 so as to place the right ventricular tip electrode 32 in the right ventricular apex so that the RV coil electrode will be positioned in the right ventricle and the SVC coil electrode 38 will be positioned in the superior vena cava. Accordingly, the right ventricular lead 30 is capable of receiving cardiac signals, and delivering stimulation in the form of pacing and shock therapy to the right ventricle.
As illustrated in
The housing 40 for the stimulation device 10, shown schematically in
To achieve left chamber sensing, pacing and shocking, the connector includes at least a left ventricular tip terminal (VL TIP) 44, a left atrial ring terminal (AL RING) 46, and a left atrial shocking terminal (AL COIL) 48, which are adapted for connection to the left ventricular tip electrode 26, the left atrial ring electrode 27, and the left atrial coil electrode 28, respectively.
To support right chamber sensing, pacing and shocking, the connector further includes a right ventricular tip terminal (VR TIP) 52, a right ventricular ring terminal (VR RING) 54, a right ventricular shocking terminal (RV COIL) 56, and an SVC shocking terminal (SVC COIL) 58, which are adapted for connection to the right ventricular tip electrode 32, right ventricular ring electrode 34, the RV coil electrode 36, and the SVC coil electrode 38, respectively.
At the core of the stimulation device 10 is a programmable microcontroller 60 which controls the various modes of stimulation therapy. As is well known in the art, the microcontroller 60 typically includes a microprocessor, or equivalent control circuitry, designed specifically for controlling the delivery of stimulation therapy and may further include RAM or ROM memory, logic and timing circuitry, state machine circuitry, and I/O circuitry. Typically, the microcontroller 60 includes the ability to process or monitor input signals (data) as controlled by a program code stored in a designated block of memory. The details of the design and operation of the microcontroller 60 are not critical to the invention. Rather, any suitable microcontroller 60 may be used that carries out the functions described herein. The use of microprocessor-based control circuits for performing timing and data analysis functions are well known in the art.
As shown in
The microcontroller 60 further includes timing control circuitry 79 which is used to control the timing of such stimulation pulses (e.g., pacing rate, atrio-ventricular (AV) delay, atrial interconduction (A-A) delay, or ventricular interconduction (V-V) delay, etc.) as well as to keep track of the timing of refractory periods, PVARP intervals, noise detection windows, evoked response windows, alert intervals, marker channel timing, etc., which is well known in the art.
The switch 74 includes a plurality of switches for connecting the desired electrodes to the appropriate I/O circuits, thereby providing complete electrode programmability. Accordingly, the switch 74, in response to a control signal 80 from the microcontroller 60, determines the polarity of the stimulation pulses (e.g., unipolar, bipolar, combipolar, etc.) by selectively closing the appropriate combination of switches (not shown) as is known in the art.
Atrial sensing circuits 82 and ventricular sensing circuits 84 may also be selectively coupled to the right atrial lead 20, coronary sinus lead 24, and the right ventricular lead 30, through the switch 74 for detecting the presence of cardiac activity in each of the four chambers of the heart. Accordingly, the atrial (ATR. SENSE) and ventricular (VTR. SENSE) sensing circuits, 82 and 84, may include dedicated sense amplifiers, multiplexed amplifiers, or shared amplifiers. The switch 74 determines the “sensing polarity” of the cardiac signal by selectively closing the appropriate switches, as is also known in the art. In this way, the clinician may program the sensing polarity independently of the stimulation polarity.
Each sensing circuit, 82 and 84, preferably employs one or more low power, precision amplifiers with programmable gain and/or automatic gain control, bandpass filtering, and a threshold detection circuit, as known in the art, to selectively sense the cardiac signal of interest. The automatic gain control enables the device 10 to deal effectively with the difficult problem of sensing the low amplitude signal characteristics of atrial or ventricular fibrillation. The outputs of the atrial and ventricular sensing circuits, 82 and 84, are connected to the microcontroller 60 which, in turn, are able to trigger or inhibit the atrial and ventricular pulse generators, 70 and 72, respectively, in a demand fashion in response to the absence or presence of cardiac activity in the appropriate chambers of the heart.
For arrhythmia detection, the device 10 utilizes the atrial and ventricular sensing circuits, 82 and 84, to sense cardiac signals to determine whether a rhythm is physiologic or pathologic. As used herein “sensing” is reserved for the noting of an electrical signal, and “diagnosis” is the processing of these sensed signals and noting the presence of an arrhythmia. The timing intervals between sensed events (e.g., P-waves, R-waves, and depolarization signals associated with fibrillation which are sometimes referred to as “F-waves” or “Fib-waves”) are then classified by the microcontroller 60 by comparing them to a predefined rate zone limit (i.e., bradycardia, normal, low rate VT, high rate VT, and fibrillation rate zones) and various other characteristics (e.g., sudden onset, stability, physiologic sensors, and morphology, etc.) in order to determine the type of remedial therapy that is needed (e.g., bradycardia pacing, anti-tachycardia pacing, cardioversion shocks or defibrillation shocks, collectively referred to as “tiered therapy”).
Cardiac signals are also applied to the inputs of an analog-to-digital (A/D) system 90. The A/D system 90 is configured to acquire intracardiac electrogram (IEGM) signals and convert the raw analog data into a digital signal. The digital signals can then be stored, in certain embodiments in memory 94, for later processing and/or telemetric transmission to an external device 102. The A/D system 90 is coupled to the right atrial lead 20, the coronary sinus lead 24, and the right ventricular lead 30 through the switch 74 to sample cardiac signals across any pair of desired electrodes.
The microcontroller 60 is further coupled to a memory 94 by a suitable data/address bus 96, wherein the programmable operating parameters used by the microcontroller 60 are stored and modified, as required, in order to customize the operation of the stimulation device 10 to suit the needs of a particular patient. Such operating parameters define, for example, pacing pulse amplitude, pulse duration, electrode polarity, rate, sensitivity, automatic features, arrhythmia diagnosis criteria, and the amplitude, waveshape and vector of each shocking pulse to be delivered to the patient's heart 12 within each respective tier of therapy.
Advantageously, the operating parameters of the implantable device 10 may be non-invasively programmed into the memory 94 through a telemetry circuit 100 in telemetric communication with the external device 102, such as a programmer, transtelephonic transceiver, or a diagnostic system analyzer. The telemetry circuit 100 is activated by the microcontroller by a control signal 106. The telemetry circuit 100 advantageously allows IEGMs and status information relating to the operation of the device 10 (as contained in the microcontroller 60 or memory 94) to be sent to the external device 102 through an established communication link 104.
In the preferred embodiment, the stimulation device 10 further includes a physiologic sensor 108, commonly referred to as a “rate-responsive” sensor because it is typically used to adjust pacing stimulation rate according to the exercise state of the patient. However, the physiological sensor 108 may further be used to detect changes in cardiac output, changes in the physiological condition of the heart, or diurnal changes in activity (e.g., detecting sleep and wake states). Accordingly, the microcontroller 60 responds by adjusting the various pacing parameters (such as rate, AV Delay, V-V Delay, etc.) at which the atrial and ventricular pulse generators, 70 and 72, generate stimulation pulses.
The stimulation device additionally includes a battery 110 which provides operating power to all of the circuits shown in
As further shown in
In the case where the stimulation device 10 is intended to operate as an implantable cardioverter/defibrillator (ICD) device, it must detect the occurrence of an arrhythmia, and automatically apply an appropriate electrical shock therapy to the heart aimed at terminating the detected arrhythmia. To this end, the microcontroller 60 further controls a shocking circuit 116 by way of a control signal 118. The shocking circuit 116 generates shocking pulses of low (up to 0.5 Joules), moderate (0.5-10 Joules), or high energy (11 to 40 Joules), as controlled by the microcontroller 60. Such shocking pulses are applied to the patient's heart 12 through at least two shocking electrodes, and as shown in this embodiment, selected from the left atrial coil electrode 28, the RV coil electrode 36, and/or the SVC coil electrode 38. As noted above, the housing 40 may act as an active electrode in combination with the RV electrode 36, or as part of a split electrical vector using the SVC coil electrode 38 or the left atrial coil electrode 28 (i.e., using the RV electrode as a common electrode).
Cardioversion shocks are generally considered to be of low to moderate energy level (so as to minimize pain felt by the patient), and/or synchronized with an R-wave and/or pertaining to the treatment of tachycardia. Defibrillation shocks are generally of moderate to high energy level (i.e., corresponding to thresholds in the range of 5-40 Joules), delivered asynchronously (since R-waves may be too disorganized), and pertaining exclusively to the treatment of fibrillation. Accordingly, the microcontroller 60 is capable of controlling the synchronous or asynchronous delivery of the shocking pulses.
If the evaluations of states 204 and 206 are affirmative, the device 10 then decreases the base rate at which therapy is provided in state 210 in an attempt to temporarily re-enable intrinsic activity of the heart 12 and the rhythm is re-evaluated in state 204. This process is repeated iteratively until either a defined minimum base rate is reached or a sufficient proportion of intrinsic activity is observed. If the determination of state 206 remains affirmative, e.g. that the intrinsic activity is not restored above the discrimination point of state 206, a state 212 follows wherein it is established that the intrinsic activity cannot be restored at the present time. Then a state 214 would follow where the attempts to automatically measure the signal amplitude are terminated and in state 216 a report would be generated indicating the inability to assess the signal amplitude.
When the determination aspect of state 204 indicates that there exists intrinsic or a sufficiently intrinsic amount of the physiological activity being sensed in a state 220, a state 222 follows wherein the physiological process is evaluated on an ongoing basis.
A particular embodiment of the invention includes this evaluation of state 222 of monitoring the sensed physiological parameter(s) especially for observation of relatively predictable patterns of activity. For example, as illustrated in
Following the monitoring of state 222, the algorithm can characterize any determined pattern and store such a pattern and characterization in memory in state 224. With the predictive capabilities of one or more determined patterns, the algorithm proceeds with a signal amplitude measurement in state 226.
The settings or adjustment of the gain of the amplifier 240 as well as the setting of the threshold regulating the output of the sensing component 244 are preferably set such that the dynamic range of the amplifier 240 and ADC 242 fully encompass the range of the physiological stimulation feeding into the amplifier 240 to avoid saturating the amplifier 240 but also such that the dynamic range is also substantially employed. If the amplifier 240 saturates, the device 10 can infer that the corresponding physiological process has reached a maximum sensed value, however the true peak magnitude of the physiological process is clipped and thus lost as the sensing as communicated to the amplifier 240 and 242 exceeds the adjusted maximum output of these components. However a substantial portion of the dynamic range is also preferably employed such that the available dynamic range is advantageously substantially employed to provide a more precise approximation of the true magnitude of the physiological process.
Thus, the settings of the amplifier 240 and ADC 242 are preferably set so as to avoid this saturation or clipping condition yet are also preferable set relatively aggressively so as to utilize a significant portion of the dynamic range of the amplifier 240 and ADC 242 to provide a higher resolution to the sensing of the physiological process. In a likewise manner, the threshold of the sensing component 244 is also preferably adjusted and set such that a physiological process of interest, such as the previously described occurrences of P waves is reliably detected with reduced occurrences of false positives and false negatives. The settings of the gain of the amplifier 240 as well as the sensing threshold of the sensing component 244 are set according to embodiments of the signal amplitude measurement algorithm 200 as described below with reference to
As will be understood, this process can be repeated in an iterative manner a number of times according to the particular application and desire for measurement resolution as well as subject to the limitations of available processing and battery capacity. In one embodiment, upon completion of these processes in state 264, the results of the test are recorded and the device 10 returns to the previously programmed settings and ongoing device operation as previously described. In certain embodiments, the device 10 can reprogram itself with an improved set of sensing parameters determined from the test.
It will be understood that the results of the signal amplitude measurement algorithm 200 can be used both as evaluative data communicated to a clinician for evaluation of the performance and therapy provided by the device 10 as well as a control variable for determination of appropriate programming of the device 10. One advantage of the signal amplitude measurement algorithm 200 is reduced need for the more demanding higher rate sampling. In particular, the device 10 employing the algorithm 200 incrementally increases the sampling rate as needed, however begins at a relatively low rate and gathers valuable information with lower demands on processing and battery capacity by the lower rate sampling which provides initial data to develop rough information which higher rate sampling can further refine.
Thus in states 270 and 272 the algorithm 200 proceeds to progressively adjust the gain and monitors the detection of the first complex as previously described for states 250 and 252 with any absence of detection being indicated by delivery by the device of therapeutic stimulation to restore the physiological activity which the device 10 has failed to detect. Similarly, in states 274, 276, 280, and 282 the algorithm 200 iteratively adjusts the sensitivity and re-evaluates the detection of the physiological process and repeats these measurements at higher sampling rates as indicated in a similar manner to that previously described for states 254, 256, 260, and 262.
Upon completion of the measurement for the first complex of the pattern, the algorithm proceeds via state 284 to repeat the states 270, 272, 274, 278, 280, and 282 for the next complex of the pattern. This process is repeated a number of times corresponding to the number of distinct complexes designated by the algorithm 200 to more accurately determine appropriate threshold setting for a physiological process exhibiting the noted relatively regular repetition of an irregular or not simply periodic pattern. Similarly as previously described for state 264, in state 286 the results of the algorithm 200 are recorded in memory and/or utilized for adjustment of the programmed settings of the device 10 as indicated.
In these embodiments, the number of cycles or occurrences of the physiological process of interest upon which the signal measurement algorithm 200 is performed can be predefined as well as be a programmable value which may have a default value, for example three cycles. Thus, in embodiments where the physiological process is relatively regular as in state 232, the algorithm 200 can be performed for three cycles which may or may not be successive cycles.
In embodiments wherein the physiological process exhibits a relatively regular irregularity, such as a condition of bigeminy, the algorithm 200 would be conducted for a similar number of cycles encompassing the repeated pattern. Thus, for example in embodiments exhibiting bigeminy, a repetition of three cycles of the measurement would encompass three pairs or six individual cycles of the physiological process of interest. It will also be appreciated that in the embodiments of irregularity or regular irregularity of the physiological process, the algorithm 200 can determine and report different sensitivity measurements corresponding to the different incidences of the physiological process. The device 10 can thus establish different gain/threshold settings for the different complexes in the repetitive patterns as shown in
It will also be appreciated that the algorithm 200 can be employed in a quasi-real time or on the fly basis as well as being performed upon stored date from previously sensed signals such as made in states 264 and 286. Thus, the determination of failure to detect a given physiological process, such as an atrial depolarization, can be performed in a virtual manner by indication for delivery of therapeutic stimulation without the requirement for actual delivery of this stimulation. It will be further appreciated that in embodiments wherein the physiological process is regular but periodically or intermittently disrupted by other factors, such as a pattern of relatively regular atrial activity which is upset by early occurrence of ventricular activity, the algorithm 200 can generate or adjust blanking periods as well as disregard the sensed signals occurring within such circumstances.
Although the above disclosed embodiments of the present teachings have shown, described and pointed out the fundamental novel features of the invention as applied to the above-disclosed embodiments, it should be understood that various omissions, substitutions, and changes in the form of the detail of the devices, systems and/or methods illustrated may be made by those skilled in the art without departing from the scope of the present teachings. Consequently, the scope of the invention should not be limited to the foregoing description but should be defined by the appended claims.
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|U.S. Classification||607/28, 600/517, 600/516, 607/27, 600/515, 600/509|
|Aug 8, 2005||AS||Assignment|
Owner name: PACESETTER, INC., CALIFORNIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:LEVINE, PAUL A.;GODAU, ARNDT;REEL/FRAME:016868/0962
Effective date: 20050803
|Jun 11, 2012||FPAY||Fee payment|
Year of fee payment: 4
|Jun 9, 2016||FPAY||Fee payment|
Year of fee payment: 8